NL2005906C2 - A mobile x-ray unit. - Google Patents
A mobile x-ray unit. Download PDFInfo
- Publication number
- NL2005906C2 NL2005906C2 NL2005906A NL2005906A NL2005906C2 NL 2005906 C2 NL2005906 C2 NL 2005906C2 NL 2005906 A NL2005906 A NL 2005906A NL 2005906 A NL2005906 A NL 2005906A NL 2005906 C2 NL2005906 C2 NL 2005906C2
- Authority
- NL
- Netherlands
- Prior art keywords
- ray
- unit
- mobile
- collimator
- unit according
- Prior art date
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/44—Constructional features of apparatus for radiation diagnosis
- A61B6/4405—Constructional features of apparatus for radiation diagnosis the apparatus being movable or portable, e.g. handheld or mounted on a trolley
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/06—Diaphragms
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
-
- H—ELECTRICITY
- H05—ELECTRIC TECHNIQUES NOT OTHERWISE PROVIDED FOR
- H05G—X-RAY TECHNIQUE
- H05G1/00—X-ray apparatus involving X-ray tubes; Circuits therefor
- H05G1/08—Electrical details
- H05G1/26—Measuring, controlling or protecting
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N2005/002—Cooling systems
- A61N2005/005—Cooling systems for cooling the radiator
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N5/1048—Monitoring, verifying, controlling systems and methods
- A61N5/1049—Monitoring, verifying, controlling systems and methods for verifying the position of the patient with respect to the radiation beam
- A61N2005/1056—Monitoring, verifying, controlling systems and methods for verifying the position of the patient with respect to the radiation beam by projecting a visible image of the treatment field
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N2005/1085—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy characterised by the type of particles applied to the patient
- A61N2005/1091—Kilovoltage or orthovoltage range photons
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N5/1077—Beam delivery systems
- A61N5/1083—Robot arm beam systems
Description
P91878NL00
Title: A mobile X-ray unit
FIELD OF THE INVENTION
The invention relates to a mobile X-ray unit comprising a base for accommodating a control unit, a power supply and a cooler and further comprising an articulated displaceable arm supporting an X-ray applicator 5 comprising an X-ray tube, said X-ray applicator being connected to the base, the X-ray tube comprising a target for generating an X-ray beam and a collimator for shaping the generated X-ray beam.
The invention further relates to a method of manufacturing the X-ray unit and a method of delivering an X-ray beam.
10
BACKGROUND OF THE INVENTION
Skin cancer, having increased incidence rate in the last decade of the 20th century, requires substantial effort from medical professionals in terms of early diagnosis, logistics and availability of suitable treatment. However, it is 15 appreciated that over 1.3 million new skin cancers are diagnosed annually and are increasing at a rate of about 5 % per year. Increased exposure to the sun without skin protection and a decreased ozone layer are regarded as the main causes of this increase - a problem estimated to be costing over 1 billion Euros in annual medical treatment expenses. Over 80% of skin cancers occur in the 20 head and neck regions with 50% occurring in patients over 60 years of age. It is expected that a portion of the senior population will double in year 2025 compared to the present demographics.
Non proliferated cancers being substantially superficial lesions may be treated in different ways. First, surgery may be envisaged. However, such 25 technique may be disadvantageous in terms of long waiting lists and complications related to post-treatment care. In addition, due to invasive character of surgery contamination of the wound by infections may present an additional risk. Secondly, irradiation using electrons of soft X-rays may be 2 envisaged. Such techniques have an advantage of being non invasive, wherein a treatment session may be as short as 2 to 4 minutes. It will be appreciated that usually the integral treatment using radiotherapeutic techniques may comprise a number of sessions.
5 Accordingly, the growing incidence of skin cancer and increasing of a share of the senior population in overall demographics pose substantial challenge on the cancer treatment logistics.
Recently, the use of a portable X-ray unit has been suggested, which may be used inside a hospital radiotherapy department. An embodiment of 10 such portable unit is described in US 2007/0076851. The known unit comprises an X-ray source provided with a filtering device having a plurality of filters rotatably arranged with respect to a focal point of the X-ray tube for changing filtering characteristics on demand. The plurality of filters is arranged in a filtering device, which is transversely arranged with respect to a longitudinal 15 axis of the X-ray tube.
It is a disadvantage of the known X-ray tube that beam characteristics due to internal geometry of the known X-ray tube may be detrimentally affected, for example leading to a broadened penumbra of the X-ray beam.
20
SUMMARY OF THE INVENTION
It is an object of the invention to provide a mobile X-ray unit having improved operational characteristics. In particular, it is an object of the invention to provide a mobile X-ray unit having improved penumbra of the X-25 ray beam and/or a reduced skin dose, when dose delivery is specified at 5 mm depth.
To this end in the mobile X-ray unit according to the invention a distance between the target and the collimator is in the range between 4 and 10 cm.
3
It is found that by setting a distance between the X-ray target and the collimator in the range of 4...10 cm, preferably to a distance of about 5 to 6 cm improved beam characteristics are achieved. For example, it is found that improved beam flatness as well as sharpened penumbra are achievable for the 5 target-collimator distance of 4...10 cm, particularly for the target-collimator distance of about 5 to 6 cm due to a relatively small focal size. For example, for the target-collimator distance of about 5 cm penumbra of 1.5 - 1.8 mm is achievable (specified for 20/80% lines).
It is appreciated that such sharpened penumbra is important 10 particularly for treating of small lesions, like skin cancers, as dose to healthy tissue, being a critical item in dose delivery planning, is minimized.
In an embodiment of an X-ray unit according to the invention, the target and the collimator are accommodated in a substantially cylindrically shaped X-ray tube having a longitudinal axis, a direction of propagation of the 15 X-ray beam being substantially parallel to said longitudinal axis.
It is found to be advantageous to arrange the anode-collimator geometry in such a way that the axis of the X-ray tube substantially coincides with a direction of propagation of the generated X-ray beam. Thus, the X-ray tube and the X-ray applicator may have the same longitudinal axis. Such 20 configuration is advantageous from mechanical perspective as balancing of the applicator on the articulated arm is simplified for a coaxial geometry. It will be appreciated that the X-ray tube, accommodated in the X-ray applicator represents a relatively slim (outer diameter of less than 10 cm) elongated cylinder (length of about 30 cm), which is preferably displaced in a vertical 25 direction for delivering the X-ray beam to the patient. Once the internal geometry of the X-ray tube is coaxial, the weight of the X-ray tube may be suitably balanced enabling easy and reproducible displacement of the articulated arm supporting the X-ray applicator.
In a further embodiment of the X-ray unit according to the 30 invention, the collimator is provided with automatic identification means 4 arranged to generate a signal in the control unit representative of collimator characteristics.
It is found to be advantageous to enable a fully automatic identification of the collimator inserted in the X-ray tube, as human errors 5 with respect to defining the field geometry may be minimized or even eliminated. For example, in case when the collimator is conceived to be provided in a receptacle, such receptacle may be provided with a resistive path whose resistivity may be changed. The collimator may then be arranged with projections adapted to cooperate with the resistive path of the receptacle for 10 changing the resulting resistivity and thus for generating a signal representative of the collimator being inserted. Preferably, the signal is made available to the control unit of the mobile X-ray unit for independent verification. Preferably, the X-ray unit comprises a set of collimators provided with respective identification means.
15 In a still further embodiment of the X-ray unit according to the invention, it is provided with a signaling means indicating generation of the X-ray beam.
It is found advantageous to provide means of signaling that the X-ray beam is on. For example, such signaling may be implemented as a suitable 20 light on the X-ray applicator. One or more light emitting diodes may be used for this purpose. It may be possible to provide a plurality of signaling means in dependence of the energy of the generated X-ray beam.
For example, for the X-ray beam of a lower portion of the spectrum (about 50 kV) a first indicator may be used, for example a first light color. For 25 an intermediate portion of the spectrum (about 60 - 65 kV) a second indicator may be used, for example a second light color. Finally, for the higher portion of the spectrum (66 - 75 kV, preferably 66 - 70 kV) a third indicator may be used, for example a third light color. It will be appreciated that a plurality of possibilities exist for indicating different spectra, including but not limited to a 30 progressive illumination of a plurality of indicators upon hardening of the 5 delivered X-ray beam. It will be further appreciated that such indication of the kV range may be allowed in the device, in a user interface or in a supplementary unit. It will be further appreciated that the named kV ranges may be scaled, for example with the factors 1,1; 1,2; 1,3; 1,4; 1,5.
5 Preferably, the signaling means comprises a light indicator arranged on the outer housing. Such arrangement of the signaling means is advantageous as the patient is made aware about the starting point and the termination of irradiation so that the patient may retain a static position during the course of treatment.
10 In a further embodiment of an X-ray unit according the invention, the cooler is arranged with piping to provide a cooling medium in a vicinity of the X-ray tube, the piping running in a space between the X-ray tube and a shielding wall associated with the X-ray tube.
It is found to be advantageous to provide a spacing between the 15 outer surface of the X-ray tube and the inner surface of the outer housing of the X-ray applicator, said spacing being at least partially filled with a coolant. It is found to be advantageous to provide circulated water as a cooling agent due to high specific heat capacity, offering improved heat transfer of water with respect to a gas. However, pressurized gas may also be used as a suitable 20 coolant. Preferably, a temperature sensor is arranged on the outer housing of the X-ray applicator for measuring actual temperature of the outer housing. The temperature sensor may be connected to the control unit for controlling the cooler and/or for controlling the high voltage supply. Should temperature rise above a pre-determined shut-off value, the control unit may be arranged to 25 disable the high voltage supply and/or to intensify the cooling mode, for example by increasing a pumping capacity of the coolant.
In a still further embodiment of the X-ray unit according to the invention a radiation detector is provided inside the outer housing for detecting the X-ray beam.
6
It is found to be advantageous to provide independent means for detecting presence of the generated X-ray beam. Preferably, the X-ray unit according to the invention comprises a primary timer which sets a time for the high voltage supply for delivering a predetermined radiation dose. The 5 radiation sensor accommodated inside the outer housing of the X-ray applicator may be part of a secondary timer circuit adapted to shut down the high voltage supply upon the event the predetermined radiation dose is delivered. In this way radiation safety control may be improved.
In a still further embodiment of the X-ray unit according to the 10 invention, the X-ray applicator comprises an exit surface conceived to be directed towards a patient, said surface being covered by an applicator cap.
It is found advantageous to provide such applicator cap, which may have many functions in use. First, the applicator cap may be used for protecting the exit surface of the X-ray applicator from intra-patient contamination. Secondly, 15 thickness of the cap in a direction of the beam propagation may be selected to be sufficient for substantially eliminating electron contamination from the X-ray beam. It will be appreciated that those skilled in the art will readily appreciate the relation between the energy of the secondary electrons emanating from the X-ray tube and a required thickness of a given material, 20 for example plastic, glass, ceramics sufficient for fully intercepting these electrons. Preferably, the applicator cap is disposable.
Thirdly, the applicator cap may function as a heat absorber for mitigating the elevated temperature of the X-ray applicator in use. As a result the patient will feel the applicator contacting the skin as a slightly warm 25 object.
In a still further embodiment of the X-ray unit according to the invention, the X-ray applicator is connected to the base using a displaceable panel, the flexible cabling running substantially in the displaceable panel.
It is found to be advantageous to provide an intermediate 30 mechanical unit connecting the base of the mobile X-ray unit and the X-ray 7 applicator for housing the flexible cables thereby preventive their entanglement. The displaceable panel may be arranged with a pre-defined travel distance with respect to a lowest achievable stand and a highest achievable stand. Such predefined travel distance may be advantageous for 5 increasing durability of the cables tubes and wiring of the X-ray unit, especially of the tubes accommodating the coolant.
In a still further embodiment of the X-ray unit according to the invention, the displaceable panel comprises a user interface for controlling the X-ray unit. Preferably, the user interface comprises a display. For example, the 10 display may be implemented as a touch screen arranged for enabling data input. Alternatively, display may be arranged for echoing data, whereas dedicated buttons or other suitable means may be provided for entering input data into the X-ray unit.
According to another embodiment of the invention there is provided 15 a method for manufacturing a mobile X-ray unit comprising a base for accommodating a control unit, a power supply and a cooler and further comprising an articulated displaceable X-ray arm supporting an X-ray applicator comprising an X-ray tube, according to the invention comprises the steps of: 20 - connecting said arm to the base using a flexible cable; arranging the X-ray tube with a target for generating an X-ray beam and a collimator for shaping the generated X-ray beam; setting a distance between the target and the collimator in the range between 4 and 10 cm.
25 Preferably, in the X-ray unit according to the invention, the target and the collimator are accommodated in a substantially cylindrically shaped X-ray applicator having a longitudinal axis, a direction of propagation of the X-ray beam being substantially parallel to said longitudinal axis. Further advantageous embodiments of the method according to the invention will be 30 discussed with reference to Figure 3.
8
In a method of delivering an X-ray beam for irradiating a superficial lesion, wherein an X-ray unit comprises a base for accommodating a control unit, a power supply and a cooler and further comprising an articulated displaceable X-ray arm accommodating an X-ray tube, said arm being 5 connected to the base using a flexible cable, the X-ray tube comprises a target for generating an X-ray beam and a collimator for shaping the generated X-ray beam, a distance between the target and the collimator being in the range between 4 and 10 cm.
The invention still further relates to an applicator cap for an X-ray 10 unit comprising an X-ray tube accommodated in an X-ray applicator, said X-ray applicator comprising an exit surface conceived to be directed towards a patient, the applicator cap being arranged for covering at least said surface. Preferably, the applicator cap is disposable. More preferably, thickness of the cap in a direction of the beam propagation is sufficient for substantially 15 eliminating electron contamination from the X-ray beam. An applicator cap may be advantageously manufactured from a substantially transparent material for enabling visualization of delineation between the exit surface of the X-ray applicator and a lesion conceived to be treated.
These and other aspects of the invention will be discussed with 20 reference to drawings wherein like reference numerals or signs relate to like elements. It will be appreciated that the drawings are presented for illustration purposes only and may not be used for limiting the scope of the appended claims.
25 BRIEF DESCRIPTION OF THE DRAWINGS
Figure la presents in a schematic way an embodiment of a mobile X-ray unit according to the invention.
Figure lb presents in a schematic way an embodiment of a displaceable panel of the mobile X-ray unit.
9
Figure lc presents in a schematic way an embodiment of displacement functionality of the applicator of the X-ray unit according to the invention.
Figure 2 presents in a schematic way an embodiment of architecture 5 of the mobile X-ray unit according to the invention.
Figure 3 presents in a schematic way an embodiment of a cross section of an X-ray applicator of the mobile X-ray unit according to the invention.
Figure 4 presents in a schematic way an embodiment of the X-ray 10 applicator of Figure 3 provided with an applicator cap.
Figure 5 presents in a schematic way an embodiment of a collimator provided with identification means.
Figure 6 presents in a schematic view an embodiment of a collimator identification system.
15 Figure 7 presents in a schematic view a further embodiment of the X-ray tube according to a further aspect of the invention.
DETAILED DESCRIPTION OF THE DRAWINGS
Figure la presents in a schematic way an embodiment of a mobile X-20 ray unit according to the invention. The mobile X-ray unit 10 comprises a base 2 comprising at least a power supply unit, a cooling system and a control unit for controlling an operation of the X-ray applicator 4 comprising an X-ray tube accommodated in an outer housing. The X-ray applicator 4 is connected with the base using flexible cables 3, which may be at least partially received in a 25 displaceable panel 5. The applicator 4 is supported by an articulated displaceable arm 4a, which may comprise a pivot for altering angulation of the applicator 4 in space. The articulated arm 4a may also be mechanically connected with the displaceable panel 5 for enabling alteration of a vertical position of the applicator 4. Preferably, the displaceable panel 5 is provided 30 with a handle 6 enabling easy manipulation thereof. The displaceable panel 5 10 may be guided along suitable rails for enabling a substantially smooth and shock-free displacement thereof.
The displaceable panel 5 may be also referred to as a displaceable mast. It is found to be advantageous to allow the mast to be displaceable along 5 a substantially upright axis with respect to the base 2. It will be appreciated that the substantially upright axis extends in a substantially vertical direction, which is generally upright. However, it will be further appreciated that the terms ‘generally upright’ or ‘substantially vertical’ may relate to a direction substantially perpendicular (+- 20 degrees) to a plane of the surface 10 on which the mobile X-ray unit is sitting.
Preferably, the base 2 is provided with a display 7 for feeding-back suitable user information. The display 7 may be arranged as a touch-sensitive screen for enabling suitable data input into the system.
15 Figure lb presents in a schematic way an embodiment of a displaceable panel of the mobile X-ray unit. In this enlarged view 10a specific elements of the displaceable panel 5 are depicted. Accordingly, a handle 6 may be implemented as a mechanical item for pulling or pushing the panel 5. Alternatively, the handle 6 may be arranged as an electrical actuator for 20 triggering motors (not shown) for displacing the panel 5. For example, when the handle 6 is pulled the motors may be activated for causing the panel 5 to displace in direction A. Pushing of the handle 6 may cause lowering of the panel 5 in direction B. Preferably, the mobile X-ray unit comprises means for limiting the movement of the panel 5. This may be advantageous for ensuring 25 mechanical stability of the system on one hand (limitation of the upper level) and, on the other hand, may be beneficial for preventing cable damage (limitation of the lower level). Preferably, the panel 5 is movable using built-in rails whose length may be chosen for limiting the displacement range of the panel 5 in a desirable way.
11
The base 2 preferably further comprises a display 7, which may function as a suitable user interface 7a. For example, the patient data, such as a photo of the patient and/or a photo of a lesion may be provided in window 7b, whereby relevant patient information, such as the date of birth, gender, dose 5 prescription and dose delivery protocol and so on may be displayed in window 7c. Buttons 7d may be provided as touch functionality for enabling entering data. Alternatively or additionally, suitable hardware switches or buttons may be provided as well.
Figure lc present in a schematic way an embodiment of 10 displacement functionality of the applicator of the X-ray unit according to the invention. In accordance with an aspect of the invention mechanics of the mobile X-ray unit is developed and realized to support a broad range of translational and rotational movements for the X-ray applicator 4.
In view 11a schematic embodiment is presented wherein the X-ray 15 applicator is in its parked position. It will be appreciated that cabling is not depicted for clarity reasons. Such position may be suitable for transport of the mobile X-ray unit towards a booth and/or for maneuvering the X-ray unit around the patient. In order to retract the X-ray applicator as close as possible to the base 2, the articulated arm 4 may be bent under the outer portion 5a of 20 the displaceable panel 5. For ensuring stability of the mobile X-ray unit during maneuvering thereof, a load block 2a close to a floor is provided for lowering an absolute position of the point of gravity of the overall construction.
View 12 presents in a schematic way a further possibility, wherein the X-ray application 4 is in one of its working positions having an X-ray exit 25 surface 8 being oriented towards a patient P. In order to suitably position the X-ray applicator with respect to the patient P, the displaceable panel may be moved to a certain dwell position located between the lowest position and the highest position of the panel 5. The articulated arm 4a may be used for suitably rotating the X-ray applicator about a rotation axis. Preferably, a 12 rotation axis is selected to coincide with a direction of emanation of the X-ray beam from the exit surface for a vertically oriented X-ray applicator.
View 13 presents in a schematic way a still further possibility, wherein the X-ray applicator 4 is to be used at a lowered position. For this 5 purpose the displaceable panel 5 may resume its lowest stand and the arm 4a may be used for orienting the X-ray applicator in a desirable way.
Figure 2 presents in a schematic way an embodiment of architecture of the mobile X-ray unit according to the invention. The mobile X-ray unit according to the invention comprises a high voltage supply, preferably adapted 10 to generate 50 - 75 kV X-rays in a suitable X-ray tube, a cooling system for cooling the X-ray tube during use and a control system for controlling electronic and electric parameters of sub-units of the X-ray unit during use. View 20 schematically depicts main units of the control system 21 and of the X-ray applicator 22.
15 The control system 21 preferably comprises a hard wired user interface 21a for enabling switching on and switching off of the high voltage supply 21b. Preferably, the high voltage supply 21b comprises a high voltage generator 21c with improved ramp-up and ramp-down characteristics. The high voltage supply is preferably operable for delivering power of about 200 W 20 in use. Preferably, the ramp-up time is of the order of 100 ms. The hard wired interface 21a, may also be arranged to automatically switch on the cooling system 2Id when the high voltage generator is switched on. In addition, the control system 21 may comprise a primary controller 21e arranged for controlling the dose delivery from the X-ray applicator in use. Such primary 25 controller 21e may be provided with a primary counter adapted to register time lapsed after the X-ray radiation is initiated. The primary counter may then automatically switch off the high voltage supply to the X-ray tube in the event a pre-determined dose is reached. It will be appreciated that the predetermined dose is at least dependent on the energy of generated X-rays and 30 the dose rate, wherein such dependence may be calibrated in advance.
13
Provided corresponding calibrated data is made available to the primary controller adequate primary dose delivery control may be achieved. Preferably, a secondary controller 2 If is provided for enabling an independent loop of dose delivery control. The secondary controller may be connected to a dose meter 5 accommodated inside the X-ray applicator in the X-ray field before the collimator. Accordingly, the dose meter may provide real-time data on actual dose delivery taking into account dose variation during ramp up and ramp down of the high voltage source. Still preferably, the control system may further comprise a safety controller 21g adapted to compare readings from the 10 primary controller 21e and the secondary controller 21g for triggering switching off of the high voltage generator 21c wherein a desired dose is delivered. In addition or alternatively, the safety controller 21g may be wired to guard emergency stop, door interlock and a generator interlock.
The X-ray applicator 22 may preferably comprise the following 15 features: an X-ray tube 22a, conceived to be housed in an outer housing (shielding) 22k. In accordance with the invention the X-ray tube is provided having a target-collimator distance of about 4-10 cm, preferably about 5 to 6 cm. The X-ray applicator may further comprise a beam hardening filter 22b selected to intercept low-energy radiation and a beam flattening filter 22c, 20 designed to intercept portions of X-ray radiation for generating a substantially flat beam profile near the exit surface of the X-ray applicator. Further, the X-ray applicator 22 may comprise one or more collimators arranged to define treatment beam geometry. Preferably a set of collimators is used, for example, having diameters of 1, 1.5, 2, 2.5, 3, 3.5, 4, 4.5, 5 cm. It will be appreciated that 25 although circular collimators are discussed, collimators of any shape, such as square, elliptic or custom made collimators are possible. It is found to be advantageous to provide the X-ray applicator 22 with automatic collimator detection means 22f adapted to automatically signal which collimator is being used. Preferably, resistive sensing is used, wherein each collimator is provided 30 with at least a couple of projections for bridging a resistive path provided in a 14 collimator receptacle. The resulting electrical resistance of the receptacle constitutes a signal representative of a collimator being used. The X-ray applicator 22 still further preferably comprises a built-in temperature sensor adapted to signal temperature of the X-ray tube and/or its shielding. The 5 signal from the temperature sensor is received by the control system which carried out analysis thereof. Should the measured temperature be elevated beyond an allowable level, an alarm signal may be generated. Optionally, a shut-off signal to the high voltage generator may be provided. The X-ray applicator 22 further comprises a radiation sensor 22h arranged inside the 10 outer housing 22k for detecting X-ray radiation which is actually being delivered by the X-ray tube. Preferably, for safety reasons the X-ray applicator 22 further comprises a non-volatile data storage 22i arranged for recording operational parameters at least of the X-ray tube. Further, to enhance radiation safety, the X-ray applicator 22 may be provided with a 15 radiation indicator 22j arranged for providing a visual and/or an audio output to the user and/or the patient regarding ON/OFF condition of the X-ray tube. It will be appreciated that the radiation indicator 22j may comprise a plurality of distributed signaling means. Preferably, at least one signaling means, for example a light emitting diode (LED) is associated with the X-ray 20 applicator 22. More preferably, the signaling means is provided on the X-ray applicator 22.
Figure 3 presents in a schematic way an embodiment of a cross section of an X-ray applicator of the mobile X-ray unit according to the invention. The X-ray applicator 30 comprises an outer housing 36 25 accommodating the X-ray tube assembly 35 provided with external shielding 35a. The X-ray applicator 30 further comprises a target 45 arranged to emit a beam of X-rays having a longitudinal propagation axis 45a. In accordance to the invention the distance between the target (anode) and the collimator 41 is in the range of 4 ... 10 cm, preferably about 5 to 6 cm. Such relatively short 30 target-collimator distance is surprisingly suitable for generating an X-ray 15 beam having a substantially narrow penumbra (1.5 - 1.8 mm for 20/80% lines) and good beam flatness.
The X-ray applicator 30 further comprises a filter 39 for hardening the X-ray beam emanating from the target 45, a beam flattening filter 40 for 5 flattening out a beam profile and collimator 33 insertable in a collimator receptacle 41.
In order to prevent overheating of the X-ray tube in use a cooling system 34 is provided, which may advantageously be arranged in spacing between the X-ray tube 35 and the shielding 35a in contact with the surface of 10 the X-ray tube 35. A suitable coolant may be provided using a pipe 31.
Preferably, the coolant is circulating and may be water, a pressurized gas or even a special oil.
The X-ray assembly 30 may further comprise a suitable radiation detector 38, connected to a radiation indicator 43. Preferably, data collected by 15 the radiation detector 38 is stored in a data storage unit 44.
In order to protect an X-ray exit surface of the X-ray applicator 30 from intrapatient contamination, an applicator cap 42 may be provided to cover at least the exit surface of the X-ray applicator 30. Preferably, the applicator cap is thick enough to fully intercept secondary electrons emanating from the X-ray 20 applicator.
Figure 4 presents in a schematic way an embodiment of the X-ray applicator of Figure 3 provided with an applicator cap. The applicator cap 42 may be manufactured from transparent glass, transparent plastic or from ceramics. It is also possible, although not preferable to manufacture the 25 applicator cap from a metal. In the latter case the applicator cap may be sterilized, however, it is preferably to use a disposable applicator cap. In view 50 of Figure 4 it is seen that the outer dimension of the X-ray applicator 51 may be larger that the outer dimension of the exit portion covered by the applicator cap 42. Although such embodiment is preferable for minimizing 16 total weight of the X-ray applicator, it is possible that the exit portion has the same dimension as the body of the X-ray applicator 51.
Figure 5 presents in a schematic way an embodiment of a collimator provided with identification means. The collimator 63 is provided with a 5 central opening 64 for defining a shape and dimension of the resulting X-ray beam emanating from the X-ray applicator 30 as is discussed with reference to Figure 3. The collimator 63 is adapted to be received in a collimator receptacle 61, which may be shaped as a suitable chamber wherein the collimator 63 is to be firmly fitted. In order to enable automatic collimator identification, the 10 collimator is provided with two projections 65a, 65b adapted to interact with a resistive path 62 provided in the collimator receptacle 61. When the projections 65a, 65b come into contact with the path 62 a net resistance of the collimator receptacle will be changed. The change in the resistance of the collimator receptacle is used as an automatic identifier of the collimator being 15 inserted in the collimator receptacle. It will be appreciated that for a set of collimators, each collimator has to be provided with a unique pair of projections leading to a distinguishable change in the net resistivity of the collimator receptacle. Those skilled in the art will readily appreciate that a plurality of pairs 65a, 65b having different respective positions on a surface of 20 the collimator may be envisaged. Alternatively, it is possible to provide each collimator with electronic identification means, for example, a chip cooperating with a plug. When the plug is plugged-in the collimator receptacle (provided with a cooperating socket) the collimator identification may be communicated to the control unit of the mobile X-ray unit.
25 Figure 6 presents in a schematic way an alternative embodiment of a collimator provided with identification means. Different embodiments of a collimator 33, shown in Figure 3, will be discussed here in more detail. The collimator 33 may be provided with an aperture 71, which may have any shape. The identification means 72a, 72b may be used for automatically 30 detecting whether a correct (i.e. intended) collimator is being inserted in the X- 17 ray applicator. For example, the identification means 72a, 72b may refer to suitable spring loaded pins arranged for interacting with a resistive body (shown in the view 33a) for causing a change in a net resistance of the resistive body. By detecting a signal representative of the absolute or relative resistance 5 of the resistive body an automatic identification of the inserted collimator may be carried out.
In view 33a a schematic embodiment of the resistive body is depicted, wherein each dot of the series 74a, 74b, 74c, 74d, 74e, 74f is attributed to a separate resistive contact circle (only few are shown for clarity).
10 The net resistive change of the resistive path 33a depends upon where the pin 72a or 72b contacts a resistive circle of the resistive circuit 33a and will change according to the contact positions. The individual collimators of the type 33, may be coded by differently positioning the contact pins 72a, 72b on the outer surface 70.
15 In alternative embodiments 33’, 33”, the contact pins 72a, 72b may be supplemented by a contact bar 76, used for locking and/or enabling an appropriate insertion of the collimator into a collimator receptacle. This feature is particularly advantageous for collimators not having rotational symmetry.
20 In a still further embodiment, the collimators and/or the pins may be color coded.
Figure 7 describes in a schematic way a further embodiment of the X-ray tube according to a further aspect of the invention. The X-ray tube 100, has a body 102 enclosing at one end an end window 104 through which the X- 25 rays pass. The end window is made from a thin sheet of Beryllium metal.
Covering the end window 104 to provide protection against the damage of the window and protection against the toxic effects of the metal is an applicator cap 106. Applicator cap 106 is preferably made from a plastics material.
In the tube body 102 a target 108 is located at between 4 -10 cm from an exit 30 surface 124, and preferably at 4-6cm from the exit surface. The target is made 18 from Tungsten metal to provide the desired X-ray spectrum. The tungsten tip of the target is mounted on a large anode assembly 110 which also serves to conduct away the heat created from the generation of the X-rays in the target. Most of the anode assembly is made from copper. The cathode 112 is located 5 slightly off-axis near the end window. Electrons emitted from the cathode are accelerated across the gap by the potential difference between the cathode and anode, in this case set at about 70kV, to the target which they impact and cause the generation of X-rays in a known manner. X-rays emitted from the target 108 pass through a beam hardening filter 122 before passing through a 10 collimator 130 and an exit surface 124 on an applicator cap 106. The collimator 130 may be housed in a suitable collimator receptacle 128.
The anode assembly 110 is mounted in the body 102 and electrically insulated from it. One of a number of known techniques and materials can be used to provide the desired level of insulation between the anode and the body 102.
15 As is also well known in the art, the production of X-rays generates large amounts of waste heat, with the result that it is necessary to cool the tube in order to maintain it at a safe temperature. Various cooling mechanisms are known and used in the art. In this embodiment, the X-ray tube is cooled by means of cooled water forced around the anode region.
20 Cooled water enters the back of the tube by means of conduits 116 and leaves by means of a second conduit 118. The water cooling circuit is a closed loop circuit, with the water leaving the tube assembly to be cooled by a remote cooler (not shown) before returning to the tube. Alternatively oil or another liquid could be used as the cooling medium. It is also known that a 25 pressurized gas is used as an effective coolant in some applications.
As is known in the art, X-rays are generated and emitted in all directions, but the shielding by the body of the tube 102 and other internal components will tend to reduce the amount of radiation emitted from the body of the tube to a minimum, with most of the radiation emitted from the end 30 window. The thickness of the shielding provided by the body is designed such 19 that it provides at least the minimum level of shielding required for safe use by the operator.
A high voltage cable assembly 120 is connected to the anode assembly 110. The high voltage cable assembly is connected to flexible cable 5 means (not shown) which in turn is connected to a high voltage power supply.
A radiation detector 114 is placed outside the path of the X-ray beam emitted from the target 108 and passing through the end window 104. This detector can be any known form of radiation detector. In this embodiment it is a known form of suitably radiation hardened semi-conductor connected to an 10 amplifier. The radiation detector 114 detects when the tube 102 is working and emitting X-ray energy. Output from the detector is connected to a control unit, the output signals from which may be used to provide an optical indication to a user of whether the tube is operating or not. By this means an X-ray detector is provided which can be used to detect whether the tube is on or off.
15 In order to enable the tube 102 to be placed accurately over a tumour, a tumour illumination means is used. The tumour illumination means comprises a plurality of lights 126 placed around the circumference of the tube near the end window. When in use, the lights shine onto the skin of the patient. Since the lights 126 are positioned around the circumference of the 20 tube body 102, at a short distance from the end of the tube they create a circle of light with a sharp cut off of the inner part of the circle. In this way, the position of the lights on the tube body 102 creates a shadow. This shadow circle is used to indicate the region which will be subject to irradiation when the X-ray tube is turned on. It should be appreciated the area within the circle 25 will not be completely dark; the ambient light will be able to enter the shadow region.
Preferably the lights 126 are white LEDs which can be bright enough to clearly illuminate the target region but do not generate amounts of heat and have very long lives. The lack of heat generation is important because the 30 lights will be in close proximity to the skin of the patient, and so it is 20 important to minimise the risk of burning or other damage to the skin. Other colours of LEDs could be used. Alternatively, other light sources could be used, such as known filament lamps or even a remote light source connected to the ring by fibre optic cables.
5 With further calibration of the radiation detector 114, it is possible to determine and calculate the X-ray dose administered to the patient during the treatment. By this means it is possible to have a real time dosimetry measurement system, in which the precise amount of radiation dose administered can be determined. Once the dose rate is known, a treatment 10 plan can be modified during treatment. This is advantageous because it enables a very accurate and carefully controlled dose of X-rays to be administered.
While specific embodiments have been described above, it will be appreciated that the invention may be practiced otherwise than as described. 15 The descriptions above are intended to be illustrative, not limiting. Thus, it will be apparent to one skilled in the art that modifications may be made to the invention as described in the foregoing without departing from the scope of the claims set out below.
Claims (25)
Priority Applications (9)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
NL2005906A NL2005906C2 (en) | 2010-12-22 | 2010-12-22 | A mobile x-ray unit. |
EP11811415.6A EP2654894B1 (en) | 2010-12-22 | 2011-12-21 | A mobile x-ray unit |
RU2013133840A RU2620931C2 (en) | 2010-12-22 | 2011-12-21 | Mobile x-ray apparatus |
BR112013015889-1A BR112013015889B1 (en) | 2010-12-22 | 2011-12-21 | MOBILE X-RAY UNIT AND METHODS FOR MAKING A MOBILE X-RAY UNIT AND DISPENSING AN X-RAY BEAM TO IRADIATE A SUPERFICIAL LESION |
PCT/NL2011/050872 WO2012087127A2 (en) | 2010-12-22 | 2011-12-21 | A mobile x-ray unit |
EP14156468.2A EP2842602B1 (en) | 2010-12-22 | 2011-12-21 | A mobile X-ray unit |
CN2011205800005U CN202715137U (en) | 2010-12-22 | 2011-12-22 | Mobile X-ray unit and applicator cap thereof |
US13/335,286 US20120195405A1 (en) | 2010-12-22 | 2011-12-22 | Mobile X-Ray Unit |
US14/971,981 US9561009B2 (en) | 2010-12-22 | 2015-12-16 | Mobile X-ray unit |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
NL2005906A NL2005906C2 (en) | 2010-12-22 | 2010-12-22 | A mobile x-ray unit. |
NL2005906 | 2010-12-22 |
Publications (1)
Publication Number | Publication Date |
---|---|
NL2005906C2 true NL2005906C2 (en) | 2012-06-25 |
Family
ID=44475000
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
NL2005906A NL2005906C2 (en) | 2010-12-22 | 2010-12-22 | A mobile x-ray unit. |
Country Status (7)
Country | Link |
---|---|
US (2) | US20120195405A1 (en) |
EP (2) | EP2654894B1 (en) |
CN (1) | CN202715137U (en) |
BR (1) | BR112013015889B1 (en) |
NL (1) | NL2005906C2 (en) |
RU (1) | RU2620931C2 (en) |
WO (1) | WO2012087127A2 (en) |
Families Citing this family (19)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
NL2005904C2 (en) * | 2010-12-22 | 2012-06-25 | Nucletron Bv | A mobile x-ray unit. |
JP2014195588A (en) * | 2013-03-29 | 2014-10-16 | キヤノン株式会社 | Radiation generation device and radiographic device |
JP6214186B2 (en) * | 2013-03-29 | 2017-10-18 | キヤノン株式会社 | Radiation generating apparatus and radiation imaging apparatus |
US10271802B2 (en) * | 2014-08-12 | 2019-04-30 | Carestream Health, Inc. | Digital x-ray imaging apparatus and method |
GB2530254A (en) * | 2014-09-12 | 2016-03-23 | Xstrahl Ltd | X-Ray system |
JP6145899B2 (en) * | 2015-07-16 | 2017-06-14 | 富士フイルム株式会社 | Radiation imaging equipment |
WO2017017949A1 (en) * | 2015-07-27 | 2017-02-02 | 富士フイルム株式会社 | Radiation-emitting device |
JP2017064360A (en) | 2015-09-29 | 2017-04-06 | 富士フイルム株式会社 | Radiation irradiation device |
US10646726B2 (en) | 2016-07-13 | 2020-05-12 | Sensus Healthcare, Inc. | Robotic intraoperative radiation therapy |
JP6325638B2 (en) * | 2016-11-17 | 2018-05-16 | 富士フイルム株式会社 | Mobile radiation generator |
US10607802B2 (en) | 2017-03-31 | 2020-03-31 | Sensus Healthcare, Inc. | Three-dimensional beam forming X-ray source |
WO2018187619A1 (en) * | 2017-04-05 | 2018-10-11 | Sensus Healthcare, Inc. | Dermatology radiotherapy system with flash treatment times |
CN111148547A (en) | 2017-07-18 | 2020-05-12 | 胜赛斯医疗有限责任公司 | Real-time X-ray dosimetry in intraoperative radiation therapy |
KR20200068653A (en) * | 2017-08-29 | 2020-06-15 | 센서스 헬스케어 인코포레이티드 | Robot IORT X-ray radiation system with calibration well |
WO2019133930A1 (en) * | 2017-12-29 | 2019-07-04 | Raydiant Oximetry, Inc. | Trans-abdominal fetal pulse oximetry and/or uterine tone determination devices and systems with adjustable components and methods of use thereof |
US11672491B2 (en) | 2018-03-30 | 2023-06-13 | Empyrean Medical Systems, Inc. | Validation of therapeutic radiation treatment |
US10940334B2 (en) | 2018-10-19 | 2021-03-09 | Sensus Healthcare, Inc. | Systems and methods for real time beam sculpting intra-operative-radiation-therapy treatment planning |
RU190316U1 (en) * | 2019-01-09 | 2019-06-26 | Федеральное государственное автономное образовательное учреждение высшего образования "Санкт-Петербургский государственный электротехнический университет "ЛЭТИ" им. В.И. Ульянова (Ленина)" | X-ray tube |
RU2740571C1 (en) * | 2020-09-21 | 2021-01-15 | Общество с ограниченной ответственностью "Научно-технический центр "МТ" (ООО "НТЦ-МТ") | X-ray mobile device |
Citations (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20030048875A1 (en) * | 2001-03-02 | 2003-03-13 | Mitsubishi Heavy Industries, Ltd. | Radiation applying apparatus |
WO2008118198A2 (en) * | 2006-10-16 | 2008-10-02 | Oraya Therapeutics, Inc. | Ocular radiosurgery |
Family Cites Families (8)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20050276377A1 (en) * | 2004-06-10 | 2005-12-15 | Carol Mark P | Kilovoltage delivery system for radiation therapy |
EP1803952B1 (en) * | 2004-10-22 | 2012-02-01 | NTN Corporation | Machined cage for cylindrical roller bearing and method of manufacturing the same |
US7263170B2 (en) | 2005-09-30 | 2007-08-28 | Pellegrino Anthony J | Radiation therapy system featuring rotatable filter assembly |
US8822934B2 (en) * | 2006-11-03 | 2014-09-02 | Accuray Incorporated | Collimator changer |
RU2334465C1 (en) * | 2006-11-20 | 2008-09-27 | Закрытое акционерное общество "ДАТА-ЦЕНТР Икс-Рэй" (ЗАО "ДАТА-ЦЕНТР-Икс-Рэй") | Mobile compact x-ray apparatus |
RU66933U1 (en) * | 2007-05-02 | 2007-10-10 | Закрытое акционерное общество "ЭЛТЕХ-Мед" | PORTABLE X-RAY DIAGNOSTIC DENTAL DEVICE |
RU81078U1 (en) * | 2008-10-06 | 2009-03-10 | Закрытое акционерное общество Инжиниринговая компания "ПРАКТИКА" | PROTON ION THERAPY SYSTEM OF ONCOLOGICAL DISEASES |
NL2005903C2 (en) * | 2010-12-22 | 2012-06-25 | Nucletron Bv | A mobile x-ray unit. |
-
2010
- 2010-12-22 NL NL2005906A patent/NL2005906C2/en active
-
2011
- 2011-12-21 EP EP11811415.6A patent/EP2654894B1/en active Active
- 2011-12-21 BR BR112013015889-1A patent/BR112013015889B1/en active IP Right Grant
- 2011-12-21 WO PCT/NL2011/050872 patent/WO2012087127A2/en active Application Filing
- 2011-12-21 EP EP14156468.2A patent/EP2842602B1/en active Active
- 2011-12-21 RU RU2013133840A patent/RU2620931C2/en active
- 2011-12-22 CN CN2011205800005U patent/CN202715137U/en not_active Expired - Lifetime
- 2011-12-22 US US13/335,286 patent/US20120195405A1/en not_active Abandoned
-
2015
- 2015-12-16 US US14/971,981 patent/US9561009B2/en active Active
Patent Citations (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20030048875A1 (en) * | 2001-03-02 | 2003-03-13 | Mitsubishi Heavy Industries, Ltd. | Radiation applying apparatus |
WO2008118198A2 (en) * | 2006-10-16 | 2008-10-02 | Oraya Therapeutics, Inc. | Ocular radiosurgery |
Non-Patent Citations (2)
Title |
---|
TOPEX, INC: "Regulatory Information", 31 December 2007 (2007-12-31), XP002656847, Retrieved from the Internet <URL:http://www.topexmedical.com/product2.html> [retrieved on 20110825] * |
TOPEX, INC: "SRT 100 Superficial Radiotherapy System for the treatment of Skin Cancer", 31 December 2007 (2007-12-31), XP002656846, Retrieved from the Internet <URL:http://www.harpell.ca/wp-content/uploads/2009/11/topexbrochure_v10.pdf> [retrieved on 20110825] * |
Also Published As
Publication number | Publication date |
---|---|
EP2654894B1 (en) | 2018-03-14 |
WO2012087127A3 (en) | 2012-12-06 |
CN202715137U (en) | 2013-02-06 |
EP2842602A1 (en) | 2015-03-04 |
RU2620931C2 (en) | 2017-05-30 |
WO2012087127A2 (en) | 2012-06-28 |
EP2654894A2 (en) | 2013-10-30 |
BR112013015889A2 (en) | 2018-06-05 |
WO2012087127A9 (en) | 2012-10-18 |
US20120195405A1 (en) | 2012-08-02 |
EP2842602B1 (en) | 2018-06-27 |
US9561009B2 (en) | 2017-02-07 |
BR112013015889B1 (en) | 2023-03-28 |
RU2013133840A (en) | 2015-01-27 |
US20160100813A1 (en) | 2016-04-14 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
NL2005906C2 (en) | A mobile x-ray unit. | |
NL2005903C2 (en) | A mobile x-ray unit. | |
NL2005904C2 (en) | A mobile x-ray unit. | |
NL2005900C2 (en) | A mobile x-ray unit. | |
US9393446B2 (en) | Mobile X-ray unit | |
NL2005899C2 (en) | A mobile x-ray unit. | |
US9724066B2 (en) | Mobile X-ray unit | |
TWI555512B (en) | A mobile x-ray unit | |
TW201350162A (en) | A mobile X-ray unit | |
TWI580457B (en) | An applicator cap,a mobile x-ray unit and a method for manufacturing the same | |
TW201350163A (en) | A mobile X-ray unit |